Lipid-polymer conjugates and liposomes

ABSTRACT

A lipid-polymer conjugate for use in forming long-circulating liposomes is disclosed. The conjugate includes a vesicle-forming lipid having covalently attached to its polar head group, one of the polymers: polyvinylpyrrolidone, polyvinylmethylether, polyhydroxypropyl methacrylate, polyhydroxypropylmethacrylamide, polyhydroxyethyl acrylate, polymethacrylamide, polydimethylacrylamide, polymethyloxazoline, polyethyloxazoline, polyhydroxyethyloxazoline, polyhydroxypropyloxazoline, or polyaspartamide. A method for preparing liposomes containing the lipid-polymer conjugate is also disclosed.

This is a continuation of application Ser. No. 08/025,602 filed Mar. 3,1993, now U.S. Pat. No. 539,619.

FIELD OF THE INVENTION

The present invention relates to a lipid-polymer conjugate, and to theuse thereof in liposomes.

References

Andreani, F., et al., (1986) J. Bioactive and Comp. Polym. 1:72-78.

Arnold, K., et al., (1990) Biochim. Biophys. Acta 1022:303-310.

Barabas, E.S. (1985) In: Encyclopedia of Polymer Science andEngineering, John Wiley & Sons, pp. 198-257.

Fuchs, O. (1982) In: Polymer Handbook (Brandrup, J., and Immergut, E.H., eds.) John Wiley & Sons, pp. 379-407.

Kawaguchi, et al., (1992) Carbohydrate Polymers 18:139-142

McCormick, C., et al., (1987) Polymer 28:2317-2323.

McDaniel, R. V., et al., (1986) Biophys. J. 49:741-752.

McLaughlin, S. and Whitaker, M. (1988) J. Physiol . 396:189-204.

Molyneux, P. (1984) In: Water soluble Synthetic Polymers: Properties andBehavior, Vol.1, CRC Press, pp. 154-163.

Needham, D.C., et al., (1992) Biochim. Biophys. Acta1108:40-48.

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Pillai, V.N.R., and Mutter, M. (1981) Naturwissenschaften 68:558-566.

Poznansky, M. J., and Juliano, R. L. (1984) Pharmacol. Rev.36:277-336.

Saba, T. M. (1970) Arch. Intern. Med. 126:1031-1052.

Saegusa, T., et al. (1972) Polym. J. 3:176-180.

Saegusa, T., et al. (1972) Macromol. 5:354-358.

Stegmann, T. S., et al. (1989) Biochem. 28:1698-1704.

Szoka, F., JR., et al., (1980) Ann. Rev. Biophys. Bioeng. 9:467.

Vegotski, A., et al., (1958) J. Amer. Chem. Soc. 80:3361.

Veronese, F. M., et al. (1990) J. Bioactive and Comp. Polym. 5:167-178.

Woodle, M. C., et al. (1992) Biophys. J. 61:902-910.

Woodle, M. C., et al. unpublished.

Zalipsky, S., et al., (1986) Polymer Preprints 27(1):1.

Zalipsky, S., et al., (1992) In: Poly (Ethylene Glycol) Chemistry:Biotechnical and Biomedical Applications (J. M. Harris, ed.) PlenumPress, pg. 347-370.

BACKGROUND OF THE INVENTION

Liposomes have the potential as versatile drug carriers in thebloodstream. Because they contain both an inner aqueous compartment andan outer lipophilic shell, liposomes can be loaded with bothwater-soluble or lipid-soluble drugs. Since liposomes can be formed ofnatural biochemical lipid, such as phospholipids and cholesterol, theycan be broken down by the body without toxic side effects (Poznansky).

Until recently, the potential of liposomes as drug carriers has beenlimited by the rapid clearance of liposomes from the bloodstream. Forexample, conventional liposomes may be largely cleared from thebloodstream within 1-2 hours after intravenous administration (Saba).

A variety of approaches for extending the circulation time of liposomeshave been proposed. Two of these have been successful in extending thehalflife of liposomes in the bloodstream by periods of up to 40-50hours. In one approach, described in co-owned U.S. Pat. No. 4,837,028,liposomes are formulated with the ganglioside G_(M1) and predominantlyrigid lipids. In another general approach, disclosed in co-owned U.S.Pat. No. 5,013,556, liposomes are coated with a layer of polyethyleneglycol (PEG) chains.

SUMMARY OF THE INVENTION

It is one general object of the present invention to provide novellipid-polymer conjugates for use in preparing liposomes having longcirculation times in the bloodstream.

It is another object of the invention to provide such long-circulatingliposomes.

The invention includes, in one aspect, a lipid-polymer conjugate capableof incorporation into liposomes. The conjugate includes (i) avesicle-forming lipid having a polar head group, and (ii) covalentlyattached to the head group, a polymer chain containing apolyvinylpyrrolidone, polyvinylmethylether, polyhydroxypropylmethacrylate, polyhydroxylpropylmethacrylamide, polyhydroxyethylacrylate, polymethacrylamide, polydimethylacrylamide,polymethyloxazoline, polyethyloxazoline, polyhydroxyethyloxazoline,polyhydroxypropyloxazoline, or polyaspartamide polymer or polymerregion. The polymer chain is characterized, in free form, by asolubility in water of at least 5% (w/v) at room temperature, and asolubility in chloroform, acetonitrile, dimethylformamide, and/ormethylene chloride of at least about 0.5% (w/v) at room temperature.

In one preferred embodiment, the polymer chain is a homopolymer of oneof the specified polymers, more preferably a homopolymer ofpolyvinylpyrrolidone, polymethyloxazoline, polyethyloxazoline, orpolyhydroxypropylmethacrylamide.

In another embodiment, the polymer is a block copolymer of one of thespecified polymers and polyethyleneglycol (PEG).

In a further embodiment, the polymer is a random copolymer formed fromvinylpyrrolidone and another monomer, such as vinyl acetate oracrylamide.

The above-listed lipid-polymer conjugates can be end-functionalized topermit attachment of therapeutically active compounds to the conjugate.

In another aspect, the invention includes a method for preparing aliposome characterized by an extended blood circulation time. The methodincludes adding to vesicle-forming lipids, between 1-30 mole percent ofthe lipid-polymer conjugate and a pharmaceutical compound to formliposomes containing vesicle-forming lipids, the lipid-polymerconjugate, and the pharmaceutical compound in entrapped form, and sizingthe liposomes to a selected size in the size range between about 0.05 to0.2 microns.

Liposomes prepared in accordance with the present invention havecharacteristic surface properties. For example, liposome surface chargeis shielded. Shielding of charge is measured by a reduction in theelectrophoretic mobility of the liposomes. Reduced mobility reflects areduction in the zeta potential of the liposomes.

The electrophoretic mobility of liposomes containing the lipid-polymerconjugate is compared to that of the same liposomes wherephosphatidylglycerol is substituted for the lipid-polymer conjugate.Both lipid-polymer conjugate and phosphatidylglycerol contribute anegative charge to the liposome surface, so both liposome preparationshave the same net surface charge. However, the electrophoretic mobilityof liposomes containing the lipid-polymer conjugate is reduced withrespect to liposomes containing phosphatidylglycerol.

These and other objects and features of the present invention willbecome more fully apparent when the following detailed description ofthe invention is read in conjunction with the accompanying drawings.

BRIEF DESCRIPTION OF THE DRAWINGS

FIG. 1 illustrates a synthetic reaction scheme for polymerizingvinylpyrrolidone;

FIG. 2 illustrates a synthetic reaction scheme for polymerizing2-methyloxazoline;

FIG. 3 illustrates a reaction scheme for polyaspartamide synthesis;

FIG. 4 illustrates a synthetic reaction scheme for randomcopolymerization of vinylpyrrolidone and methyl acrylate monomers;

FIG. 5 illustrates a synthetic reaction scheme for preparing a blockcopolymer with polyvinylpyrrolidone and polyethyleneglycol segments;

FIG. 6 illustrates coupling of polyvinylpyrrolidone to a phospholipid byuse of N-hydroxysuccinimide; and

FIG. 7 illustrates conversion of the terminal hydroxyl group ofpolymethyloxazoline to a carboxylic acid group, and coupling of thepolymer to a phospholipid through this carboxyl group.

DETAILED DESCRIPTION OF THE INVENTION

I. Definitions

Unless indicated otherwise, the terms below have the followingdefinitions:

"Homopolymers" are polymers which have one monomer in their composition.

"Copolymers" are polymers which have more than one type of monomer intheir composition. Copolymers may be block copolymers or randomcopolymers. Block copolymers contain alternating blocks (segments) ofdifferent homopolymers. Random copolymers contain random sequences oftwo or more monomers.

The term "vesicle-forming lipid" is intended to include any amphipathiclipid having a hydrophobic moiety and a polar head group, and which (a)by itself can form spontaneously into bilayer vesicles in water, asexemplified by phospholipids, or (b) is stably incorporated into lipidbilayers in combination with other amphipathic lipids, with itshydrophobic moiety in contact with the interior, hydrophobic region ofthe bilayer membrane, and its polar head group moiety oriented towardthe exterior, polar surface of the membrane.

A polymer is "soluble" in water if the polymer (either a homopolymer orcopolymer) is soluble to at least 5% by weight at room temperature at apolymer size between about 20-150 subunits.

A polymer is "soluble" in a polar organic solvent, which may bechloroform, acetonitrile, dimethylformamide, and/or methylene chloride,if the polymer (either a homopolymer or copolymer) is soluble to atleast 0.5% by weight at room temperature, at a polymer size betweenabout 20-150 subunits.

II. Preparation of Polymer-Lipid Conjugate

The lipid-polymer conjugate of the invention includes (i) avesicle-forming lipid having a polar head group, and (ii) covalentlyattached to the head group, a polymer chain having selected solubilityproperties, as described below. This section describes the preparationof the conjugate.

A. Vesicle-Forming Lipid

The vesicle-forming lipids used in the lipid-polymer conjugate forforming liposomes of the invention may be selected from a variety ofsynthetic vesicle-forming lipids or naturally-occurring vesicle-forminglipids. Typically, these lipids may include phospholipids, sphingolipidsand sterols.

An important feature of the vesicle-forming lipid used in thelipid-polymer conjugate is that the lipid contain a chemical group atits polar head group suitable for covalent attachment of a polymerchain. The polar head group may contain, for example, an amine group,hydroxyl group, aldehyde group or a carboxylic acid group.

Additionally, the vesicle-forming lipid of the lipid-polymer conjugateis selected to achieve a specified degree of fluidity or rigidity, tocontrol the stability of liposomes in serum and to control the rate ofrelease of entrapped drug from liposomes in the blood stream. Theselipids may also be selected, in lipid hydrogenation characteristics, toachieve desired liposome preparation properties. It is generally thecase, for example, that more fluidic lipids are easier to formulate andsize by extrusion than more rigid lipid components.

A preferred embodiment of the vesicle-forming lipid of the lipid-polymerconjugate is a lipid having two hydrocarbon chains, typically acylchains, and a polar head group containing a chemical group. Included inthis class are the phospholipids, such as phosphatidylcholine (PC),phosphatidylethanolamine (PE), phosphatidylglycerol (PG), phosphatidicacid (PA), phosphatidylinositol (PI), and sphingomyelin (SM), where thetwo hydrocarbon chains are typically between about 14-22 carbon atoms inlength, and have varying degrees of unsaturation.

Phosphatidylethanolamine (PE) is an example of a phospholipid which ispreferred for the invention since it contains a reactive amino groupwhich is convenient for lipid coupling to polymers. One preferred PEillustrated in the examples is distearyl PE (DSPE).

B. Polymers

The polymer chain in the conjugate is formed from polyvinylpyrrolidone,polyvinylmethylether, polyhydroxypropyl methacrylate, polyhydroxyethylacrylate, polymethacrylamide, polydimethylacrylamide,polymethyloxazoline, polyethyloxazoline, or polyaspartamide polymers.The polymer chain preferably contains between 20 to 150 monomersubunits, more preferably 40 to 100 monomer subunits.

The chain may be a homopolymer of the selected polymer or a random orblock copolymer containing one or more blocks of the selected polymerspaced by blocks or single subunits of a second polymer. The secondpolymer may be another of the above-specified polymers or anotherpolymer type, with the limitation that the random or block copolymermeet the following solubility constraints which are important to theproperties of the lipid-polymer conjugate in liposomes, as discussedbelow.

Specifically, the copolymer composition is such that the polymer ischaracterized, in free form (unattached to the lipid moiety), by asolubility in water of at least 5% (w/v) at room temperature, and asolubility in chloroform, acetonitrile, dimethylformamide, and/ormethylene chloride of at least about 0.5% (w/v) at room temperature.

Preferred homopolymers and copolymers, and their methods of synthesiswill now be considered.

1. Homopolymer Solubility Properties.

A preferred homopolymer in the invention is polyvinylpyrrolidone (PVP).This polymer is readily soluble (at least 5% by weight) in cold water,as indicated in Table 1 below (Molyneux). The polymer is also soluble(at least 0.5% by weight) in one or more of the polar solventschloroform, acetonitrile, dimethylformamide, and/or methylene chloride.The PVP polymers shown in Table 1 have subunit numbers ranging fromabout 60 (PVP7000) to 3500 (PVP400,000). As defined herein, thespecified solubilities in water and a polar organic solvent aredetermined for a polymer having the desired polymer size of betweenabout 20-150 subunits. Therefore, the solubilities listed in Table 1 forpolymers of larger sizes, such as a PVP chain with 3,500 subunits,likely reflect minimum solubility values for polymers of smaller sizes,such as PVP chains with about 20-150 subunits.

                  TABLE 1                                                         ______________________________________                                        PVP10000     water         10    wt %                                         PVP40000     chloroform    3     wt %                                         PVP7000      methanol      2     wt %                                         PVP400000    dimethylformamide                                                                           1     wt %                                         PVP20000     cyclohexanone 0.5   wt %                                         ______________________________________                                    

Considering the solubility properties of other homopolymers mentionedabove, poly(dimethylacrylamide) is soluble in water and organicsolvents, such as methanol, ethanol, and dioxane. Polymethacrylamide issoluble in water, methanol, ethylene glycol, and acetone, while it isinsoluble in hydrocarbons and diethyl ether (Molyneux).

Polyethyl-and polymethyloxazolines are soluble in water, and soluble inacetonitrile, chloroform, and dimethylformamide (Molyneux).

Polyvinylmethylether is soluble in water, and also in alcohols, amines,esters, aromatic hydrocarbons, and chlorinated hydrocarbons (Molyneux).

Polyaspartamide is a polymer derived from aspartic acid and renderedsoluble in water by reaction with ethanolamine which generates hydroxylgroups along the polymer chain. This polymer is soluble in water anddimethylformamide (Neri).

Polyhydroxypropyl methacrylate and polyhydroxyethyl acrylate are alsosoluble in water and one or more of the specified polar organicsolvents.

Additionally, the homopolymer can be a derivatized cellulose, such ascarboxymethylcellulose, hydroxypropylcellulose, orhydroxyethylcellulose. In underivatized cellulose intermolecularhydrogen-bonding results in decreased solubility of cellulose in water.Derivatizing cellulose hydroxyl groups decreases hydrogen-bonding, andas a consequence increases cellulose solubility in water. Derivatives ofcellulose usually are formed with varying degrees of substitution at thehydroxyl groups of C-2, C-3, and C-6.

Preferred derivatized celluloses exhibit the following solubilities. Forexample, hydroxypropylcellulose and hydroxyethylcellulose are soluble inwater, chloroform, acetone, pyridine, cyclohexanone and are not solublein ethanol, diethyl ether and aliphatic hydrocarbons. Cellulose acetateis soluble in water, methylene chloride, chloroform, tetrahydrofuran,among others. It is insoluble in aliphatic hydrocarbons, ethanol, andbenzene (Fuchs).

Alternatively, the polymers in the invention may be copolymers whichincorporate the above-named monomers, either as block or randomcopolymers. For examples, a polymer containing a high percentage ofvinylpyrrolidone and another subunit, such as vinylmethylether, methylacrylate, hydroxypropyl methacrylate, hydroxyethyl acrylate,methacrylamide, and dimethylacrylamide, may be prepared by radicalpolymerization methods used in PVP synthesis.

Preferred block copolymers with the requisite solubility characteristicsare formed to contain one or more alternating blocks of PEG and one ofthe homopolymers disclosed above. In a preferred embodiment theheteropolymer is a block copolymer consisting of alternating PVP and PEGblocks, or a single blocks of each.

2. Homopolymer Synthesis.

Polyvinylpyrrolidone (PVP), an example of an N-vinyl amide polymer, willbe discussed in detail as a preferred embodiment of this aspect of theinvention. PVP can be synthesized by free radical, anionic, or cationicpolymerization of vinyl pyrrolidone (VP) monomers. Preferably, themonomer is polymerized by the free radical route in the presence of afree radical initiator, such as hydrogen peroxide orazobisisobutyronitrile (AIBN).

As described in Example 1 and illustrated in FIG. 1, VP monomers areincubated with mercaptoacetic acid (MACA) and AIBN to favor synthesis ofPVP with a molecular weight of about 6,000. MACA is used in thepolymerization reaction to generate a chemical group, a carboxyl group,at a polymer free end for coupling to a vesicle-forming lipid.Additionally, MACA concentrations are varied to synthesize polymers of adesired length. For example, a 0.2 molar MACA concentration is used tosynthesize PVP polymers of a molecular weight of about 6,000 daltons.MACA also decreases product heterogeneity, and product may not needfurther purification by size fractionation (Andreani, Veronese).Alternatively, other mercaptans, such as mercaptoethanol (ME) ormercaptopropanoic acid (MPA), can replace MACA in the polymerizationreaction to generate an appropriate terminal group.

A similar free-radical polymerization method is suitable for thesynthesis of polyvinylmethylether, polyhydroxypropyl methacrylate,polyhydroxyethyl acrylate, polydimethyl acrylamide, orpolymethacrylamide for generating polymers suitable for this invention.

FIG. 2 illustrates a synthetic reaction scheme for a polymerization of2-methyl-oxazoline (MOZ). In this reaction, MOZ polymerization occurs bya cationic polymerization mechanism. MOZ polymerization is initiated bymethyl tosylate which catalyzes a ring opening reaction of2-methyl-oxazoline. The polymerization reaction is propagated by thepolymer "live end" which can cause further 2-methyl-oxazolinering-opening reactions. After the polymerization reaction an aqueousworkup generates a hydroxyl group by displacement of the tosylate groupat a polymer end (Saegusa). This hydroxyl group is used for polymerattachment to a vesicle-forming lipid. Reaction conditions are discussedin Example 2.

Nucleophilic reagents, other than water, can be used to provide otherfunctional groups at a polymer end. For example, use of a diamine wouldgenerate an amine group at the free end. A similar procedure is used forthe synthesis of poly(2-ethyl-oxazoline).

FIG. 3 illustrates a synthetic reaction scheme for the formation ofpolyaspartamide. Aspartic acid is polymerized by heating for 2-4 hoursat 200° C. to generate polysuccinimide with an average molecular weightof 11,000 (Vegotski). Polysuccinimide is reacted with ethanolamine. Thisresults in ring-opening of succinimide groups of the polymer chain togenerate poly(hydroxyethyl-(D,L-aspartamide). The terminal carboxylicacid groups are coupled to a vesicle-forming lipid after activation ofeither or both carboxylic acid groups at one polymer end.

Other homopolymer candidates can be synthesized as follows. To generatecellulose derivatives, cellulose is reacted with chloroacetic acid toform carboxymethylcellulose or with ethylene oxide to formhydroxyethylcellulose. To maximize solubility of derivatized cellulosesin water, it is usually necessary to partially hydrolyze the fullyderivatized cellulose (Kawaguchi, McCormick). In this manner polymerscontaining between 40 and 100 sugar units can be generated. This is thedesired length for purposes of the invention.

3. Random Copolymer Synthesis.

FIG. 4 shows the formation of a random copolymer of VP and acrylamide(AA) monomers. As described for the polymerization of VP monomerscopolymerization reactions are performed in the presence of a freeradical initiator and a terminator such as MACA to introduce an endfunctional group and to decrease product heterogeneity. The ratio ofindividual monomers in a polymerization reaction mixture is dependent onthe reactivity of each monomer to free radical polymerization and to themonomer ratio desired in the polymerization product (Barabas).

VP copolymerizes readily with a wide variety of other monomers, such asethyl acrylate, methyl acrylate, methyl methacrylate, maleic anhydride,dimethylaminoethyl methacrylate, acrylamide, methacrylamide, ethylene,vinyl propionate, vinyl caprolactam, and methyl vinyl ketone. Themonomers copolymerized with VP preferably possess similar solubilitycharacteristics as does VP, such as methacrylamide monomer.

Alternatively, the monomers copolymerized with VP may possess differentsolubility characteristics, such as methylmethacrylate monomers. Themethylmethacrylate monomer content of the random copolymer is selectedso that the polymer product has solubility characteristics similar tothose of PVP.

4. Block Copolymer Synthesis.

FIG. 5 illustrates the synthesis of a block copolymer containing a PVPand a PEG block. A short PVP polymer chain prepared as described abovecan be coupled to a bifunctionalized PEG polymer chain containingterminal amine and carboxylic groups by standard coupling methods togenerate an amide linkage (Zalipsky, 1986).

Other block copolymers containing blocks of PEG and blocks of any of theother homopolymers disclosed possessing the requisite solubilityproperties can be formed in a similar manner by reacting a homopolymercontaining a chemical group at one of its ends with a bifunctionalizedpolymer chain.

Heteropolymers containing more than one alternating block of PEG and anyof the disclosed homopolymers can be formed by reacting bifunctionalizedPEG chains with bifunctionalized homopolymer chains in the presence of alinking reagent, such as a diisocyanate. The heteropolymer productshould possess the requisite solubility properties. In a preferredembodiment the heteropolymer contains several alternating blocks of PVPand PEG.

C. Coupling Methods

In general the covalent attachment of polymers to a vesicle-forminglipid is accomplished by activation of chemical groups at one polymerend prior to reaction with a vesicle-forming lipid. A terminal hydroxyl,amine or carboxyl group may be activated for coupling to the lipid bymonofunctional activating agents, such as N-hydroxysuccinimide,ethylchloroformate, DCCD, Woodward's Reagent K, cyanuric acid andtrifluoromethanesulfonyl chloride among others. A number of bifunctionalcrosslinking reagents containing groups with different reactivities,such as some diisocyanates, may also be used to activate polymers priorto coupling to lipid components.

A preferred method for activating a PVP polymer for attachment to aphospholipid is illustrated in FIG. 6. In this reaction the terminalcarboxyl group of the polymer is activated by reaction withN-hydroxysuccinimide. After this activation step the polymer is reactedwith an amino group-containing phospholipid, suchphosphatidylethanolamine, to generate the polymer derivatizedvesicle-forming lipid which is part of the composition of the invention.

Methods known to one skilled in art are available for activation ofterminal hydroxyl groups (Zalipsky, 1992). In one such method,illustrated in FIG. 7, polymethyloxazoline is reacted with succinicanhydride to generate a carboxyl group at a polymer end. The terminalcarboxyl group of the polymer is activated by reaction withN-hydroxysuccinimide. After this activation step the polymer is reactedwith an amino group-containing phospholipid, such asphosphatidylethanolamine, forming the desired product.

Most of the polymers described in this invention can be coupled byeither of the above described coupling methods. For coupling ofderivatized celluloses, the polymers are incubated in the presence of anamine group-containing lipid without any prior activation step. Couplingcan occur at the reducing end of the polysaccharide chain by reductiveamination.

III. Liposome Composition

The polymer-lipid conjugate of the invention is used in preparingliposome compositions designed for use in delivering a drug via thebloodstream. In one embodiment the polymer-lipid conjugate, whenincorporated at a mole ratio of preferably 1-30 mole percent in theouter lipid layer of the liposomes, forms a polymer layer which iseffective to extend the blood circulation time of the liposomesseveralfold over that of the liposomes lacking the polymer-lipidconjugate.

A. Lipid Components

The liposome is composed of underivatized vesicle-forming lipids andpolymer-lipid conjugates which have been described above. Theunderivatized vesicle-forming lipids will form the bulk of the vesiclestructure in the liposome.

Generally, these vesicle-forming lipids include any amphipathic lipidshaving hydrophobic and polar head group moieties, and which (a) can formspontaneously into bilayer vesicles in water, as exemplified byphospholipids, or (b) are stably incorporated into lipid bilayers, withits hydrophobic moiety in contact with the interior, hydrophobic regionof the bilayer membrane, and its polar head group moiety oriented towardthe exterior, polar surface of the membrane.

The vesicle-forming lipids of this type are preferably ones having twohydrocarbon chains, typically acyl chains, and a polar head group.Included in this class are the phospholipids, such asphosphatidylcholine (PC), PE, phosphatidic acid (PA),phosphatidylinositol (PI), and sphingomyelin (SM), where the twohydrocarbon chains are typically between about 14-22 carbon atoms inlength, and have varying degrees of unsaturation.

The above-described lipids and phospholipids whose acyl chains have avariety of degrees of saturation can be obtained commercially, orprepared according to published methods. Other lipids that can beincluded in the invention are glycolipids and sterols, such ascholesterol.

The second type of lipid in the liposome composition is thepolymer-lipid conjugate described in Section IIA. This polymer-lipidconjugate is included at a molar concentration sufficient to extend theblood circulation time of the liposomes severalfold over that of theliposomes lacking the polymer-lipid conjugate. The lipid conjugate istypically included at 3-10 mole percent, preferably about 5 molepercent.

One preferred embodiment of the polymer-lipid conjugate is a PVPpolymer-derivatized distearylphosphatidylethanolamine (PVP-DSPE). ThePVP chain is preferably a PVP chain having a molecular weight between2,000-17,000 daltons, more preferably between 4,500 and 11,000 daltons.The lipid is preferably a PE, such as DSPE.

Another preferred embodiment of the polymer-lipid conjugate is apolymethyloxazoline-derivatized distearylphosphatidylethanolamine(PMOZ-DSPE). The polymethyloxazoline chain is preferably a chain havinga molecular weight between 2,000-16,000 daltons, more preferably between4,000 and 11,000 daltons.

B. Liposome Preparation

The liposomes may be prepared by a variety of techniques, such as thosedetailed in Szoka et al, 1980. One method for preparing drug-containingliposomes is the reverse phase evaporation method described by Szoka etal and in U.S. Pat. No. 4,235,871. In this method, an organic solutionof liposome-forming lipids is mixed with a smaller volume of an aqueousmedium, and the mixture is dispersed to form a water-in-oil emulsion,preferably using pyrogen-free components. The drug or otherpharmaceutical agent to be delivered is added either to the lipidsolution, in the case of a lipophilic drug, or to the aqueous medium, inthe case of a water-soluble drug.

After removing the lipid solvent by evaporation, the resulting gel isconverted to liposomes, with an encapsulation efficiency, for awater-soluble drug, of up to 50%. The reverse phase evaporation vesicles(REVs) have typical average sizes between about 0.2-0.4 microns and arepredominantly oligolamellar, that is, contain one or a few lipid bilayershells. The REVs may be readily sized, as discussed below, by extrusionto give oligolamellar vesicles having a maximum selected size preferablybetween about 0.05 to 0.2 microns.

To form MLV's, a mixture of liposome-forming lipids of the type detailedabove dissolved in a suitable solvent is evaporated in a vessel to forma thin film, which is then covered by an aqueous medium. The lipid filmhydrates to form MLVs, typically with sizes between about 0.1 to 10microns. Typically, MLVs are sized down to a desired size range of 0.5or less, and preferably between about 0.05 and 0.2 microns by extrusion.

One effective sizing method for REVs and MLVs involves extruding anaqueous suspension of the liposomes through a polycarbonate membranehaving a selected uniform pore size, typically 0.05, 0.08, 0.1, 0.2, or0.4 microns (Szoka). The pore size of the membrane corresponds roughlyto the largest sizes of liposomes produced by extrusion through thatmembrane, particularly where the preparation is extruded two or moretimes through the same membrane.

Alternatively, the REV or MLV preparations can be treated to producesmall unilamellar vesicles (SUVs) which are characterized by sizes inthe 0.04-0.08 micron range. SUVs may be useful, for example, intargeting a tumor tissue which permits selective passage of smallparticles, typically less than about 0.1 micron, through the capillarywalls supplying the tumor. As noted above, SUVs may be formed readilyfrom fluid vesicle-forming lipids.

After final sizing, the liposomes can be treated, if necessary, toremove free (non-entrapped) drug. Conventional separation techniques,such as centrifugation, diafiltration, and molecular-sievechromatography are suitable. The composition can be sterilized byfiltration through a conventional 0.45 micron depth filter.

Although the polymer-lipid conjugate of the invention is preferablyincluded in the lipid components used in forming liposomes, theconjugates may alternatively be incorporated into the outer liposomelayer by diffusion into preformed liposomes. Typically, this is done byincubating preformed liposomes in the presence of the conjugate (whichcan exist in solution in micellar form) until a desired concentration ofthe conjugate has been taken up in the liposomes. The suspension mayadditionally contain surfactants, such as deoxycholate, to facilitatediffusion of the conjugate into liposomes. The surfactant can be removedsubsequently, e.g., by dialysis.

The liposomes may be prepared to include surface-bound ligand molecules,such as antibodies, which are effective to bind specifically and withhigh affinity to ligand-binding molecules, such as antigens, which arelocalized specifically on target cells. As an example, the ligandmolecules may be tumor-specific antibodies, for binding totumor-specific antigens on tumor cells.

A variety of methods for coupling ligands to the surface of liposomesare known. One method includes incorporation of preformedligand-derivatized lipid components into liposomes. Alternatively,ligands may be coupled to activated ends of polymer chains in apreformed liposome.

C. Surface Shielding Properties

The derivatized lipid-polymer conjugates prepared as above can befurther selected for their ability to shield surface charge onliposomes. The shielding of surface charge can be measured, for example,by changes in the electrophoretic mobility of negatively chargedliposomes, according to methods described below.

Table 2 shows the surface charge, zeta potential and the distributionratio between the mononuclear phagocytic system (MPS) and blood forliposomes containing 3 mole percent of the lipid components at the leftin the table. Here PC refers to phosphatidylcholine, PS refers tophosphatidylserine, PG refers to phosphatidylglycerol, G_(Ti), G_(D1a),and G_(M1) refer to different gangliosides, and PEG-DSPE refers todistearylphosphatidyl-ethanolamine derivatized by PEG.

                  TABLE 2                                                         ______________________________________                                                 MPS/Blood                                                                     level      Surface Potential (mV)                                    Lipid      (24 hr)      Surface Charge                                                                            Zeta                                      ______________________________________                                        PC         8.6          0           0                                         PS         188          -6          -8                                        PG         123          -6          -8                                        G.sub.Ti                -4.6        -17                                       G.sub.D1a               -6          -12                                       G.sub.M1   3.0          -3.4        -5                                        PEG-DSPE   0.7          Equal to PG -1.3                                      ______________________________________                                    

Ratios of liposomes in the mononuclear phagocytic system (MPS) and inthe blood are used as a measure of the blood circulation lifetime of theliposomes in vivo, where a lower ratio indicates less uptake by the MPSand longer circulation in the bloodstream. The ratios shown in the tablewere determined for liposomes distribution 24 hours after intravenousadministration, for example by the method described in U.S. Pat. No.4,920,016. As seen, all of the formulations except the one containingPEG-DSPE gave MPS/blood ratios significantly above 1.

The surface charge values given in the table were calculated by standardmethods, such as those described in McDaniel et al., and reflect thesurface density of negative charges on the liposomes. It is noted thatthe surface charge has been determined with respect to selected ionicstrength and pH of the liposome in addition to the mole content of thecharged lipid components.

The zeta potential values in the table provide a measure of the apparentcharge on the outer surface of the liposomes. These values aredetermined from the electrophoretic mobility of the liposomes, accordingto known methods (Woodle). The zeta potential values thus reflect thecharge on the liposomes seen by the electric field duringelectrophoresis. A less negative zeta potential means that the liposomeshave a lower apparent surface charge, as determined from a reducedmigration rate in an electric field.

If the zeta potential values are lower than the surface charge valuesfor any liposome formulation, the reduced zeta potential is likelyindicative of screening of the surface charge. There is no chargeshielding effect observed in liposomes containing PS, PG, G_(T1), orG_(D1a). The liposome formulation containing PEG-DSPE, however, showscharge shielding. The zeta potential of -1.3 mV for PEG-DSPE liposomes(Woodle) represents a severalfold drop in negative charge over liposomescontaining phosphatidylglycerol (PG) (zeta potential of -8 mV).Liposomes containing either PG or DSPE have the same surface chargedensity as do PEG-DSPE liposomes, but the charge is not shielded. Thischarge shielding effect correlates with the low MPS/blood ratio observedfor this formulation.

Liposomes containing G_(M1) also exhibit charge shielding, but not tothe same extent as do PEG-DSPE liposomes. G_(M1) contains a negativelycharged sialic acid group that extends away from the liposome surfaceinto the aqueous phase. If the sialic group were located on the liposomesurface, the surface charge would be expected to be comparable to thatof PG or PEG-DSPE liposomes (-6 mV). However, the surface charge valueis lower as expected from the location of the negative charge (-3.4 mV).

The zeta potential of G_(M1), therefore, is reduced (-5 mV) whencompared with a value of( -6 mV) which is the true liposome charge.Also, the zeta potential is lower than for PG liposomes even though thenegative charges are closer to the zeta potential determining plane(Mclaughlin, McDaniel). The MPS/blood ratio for G_(M1) liposomes isreduced compared to that of PG or PS liposomes, but is not as low as forPEG-DSPE liposomes.

More generally, in accordance with one aspect of the invention, thelipid-polymer conjugate employed in the liposome composition of theinvention is preferably one that is effective to shield liposome chargeto an extent effective to reduce the electrophoretic mobility of theliposomes with respect to the same liposomes in which a lipid with ,such as phosphatidylglycerol, is substituted for the added conjugate.The lipid-polymer conjugate and phosphatidylglycerol both contain asingle negative charge at its lipid polar head group and contribute tothe surface charge on the liposomes.

IV. Utility

As noted above, the polymer layer formed on liposomes or on othercolloidal drug delivery systems by the lipid-polymer conjugate functionsto extend the blood circulation time of the liposomes severalfold. Theenhanced blood circulation time, in turn, will allow a variety oftherapeutic uses which are not effective in conventional, rapidlycleared liposomes. Some of these new therapeutic uses include:

1. Prolonged delivery of a drug by release from the particles, as theycirculate in the bloodstream over an extended time.

2. Treatment of solid tumors. The long circulation time allows theparticles to reach a tumor targeting site via the bloodstream, and toextravasate into the tumor region.

3. Treatment of infection or inflammation. As above, the longcirculation time allows the particles to reach a site of infection orinflammation, via the bloodstream, and to extravasate into the region ofinfection.

A critical feature of the polymer layer on the liposome, as indicatedabove, is that the polymers forming the layer are soluble in an aqueousmedium, but also soluble in one or more of a variety of polar organicsolvents. Polymer solubility in water permits the polymer chains toextend away from the liposome surface out into the aqueous shellsurrounding the liposome, and to effectively "fill" the aqueous shell.Polymer solubility in a variety of organic solvents and water suggeststhat the polymer chains are conformationally flexible, and thus are ableto create a uniform local concentration of polymer chains around theouter surface of the liposomes forming an effective barrier tointeractions between the liposome surfaces and blood components involvedin liposome uptake from the blood.

The following examples illustrate methods of preparing lipid-polymerconjugates which can be incorporated in liposome compositions to enhanceliposome circulation times in the bloodstream. The examples are intendedto illustrate specific lipid-polymer conjugate preparations, but are inno way intended to limit the scope thereof.

EXAMPLE 1 Preparation of PVP-DSPE Conjugate

The polymerization of PVP, and attachment of PVP to DSPE described inthis example is illustrated in FIGS. 1 an 6, respectively.

A. PVP Polymerization

A mixture of 25 g (0.23 mole) of N-vinyl-2-pyrrolidone, with 0.7 ml (10mmole) mercaptoacetic acid (in a 70% aqueous solution) and 125 mg (0.76mmole) of AIBN is diluted to 50 ml with methanol and kept at 60° C. withstirring under a nitrogen atmosphere. After 24 hours, 100 ml methylenechloride is added. The solution is dried over anhydrous sodium sulfate,filtered and poured with stirring into an excess of dry ether. Thepolymer is purified by dissolving in methylene chloride andreprecipitating into an excess of dry ether.

Product is further purified by size fractionation using a Bio Gel P60column (5×50 cm) and water as the mobile phase. PVP polymers with amolecular weight of approximately 6,000 daltons (about 53 monomer units)are isolated.

B. PVP Attachment to DSPE

To activate the carboxylic acid of PVP for coupling to the amine groupof DSPE the following protocol is utilized. To a solution of PVP6000, 10g, 1.7 mmole in 50 ml of N,N-dimethylformamide (DMF) cooled to 10° C.,and 0,575 g, 5 mmole of N-hydroxysuccinimide in DMF, and dicyclohexylcarbodiimide (1.032 g, 4.6 mmole) in DMF, are added. The solution isstirred overnight and the temperature is allowed to increase to roomtemperature. After removal of the precipitated dicyclohexylurea byfiltration, the solution is concentrated to dryness under high vacuum.The residue is taken up in 50 ml of methylene chloride and the solutionadded dropwise to stirred diethyl ether (500 ml). The white precipitateis recovered by filtration and reprecipitated twice from methylenechloride/diethyl ether.

For attachment of PVP6000 to the polar head group of DSPE, to achloroform solution (10 ml) of N-hydroxysuccinimide-ester PVP (0.8mmole) is added DSPE (0.52 g, 0.70 mmole) TEA (0.2 ml, 1.4 mmole) to thereaction mixture. The mixture is maintained in an oil bath heated to40°-45° C. for 2 hours. The formation of product is confirmed by TLC onsilica plates (chloroform/methanol/water/concentrated ammoniumhydroxide, (21.5/70/8/0.5).

EXAMPLE 2 Preparation of Polymethyloxazoline-DSPE Conjugate

The polymerization of 2-methyl-2-oxazoline, and attachment of thepolymer to DSPE described in this example is illustrated in FIGS. 2 and7, respectively.

A. Polymerization of 2-methyl-2-oxazoline

Cationic polymerization of 2-methyl-2-oxazoline (MOZ) is carried out byusing methyltosylate (MET) as an initiator. To MOZ (3.2 mmole) ia addedMET (0.07 mmole) in 1 ml acetonitrile. The reaction proceeds for 5 hoursat 80° C. The polymerization product is precipitated two times withdiethyl ether. The polymerization product is purified by sizingchromatography to isolate polymer species with about 30 to 60 monomerunits. This corresponds to a molecular weight of about 2000 to 4000.

The product is dissolved in water to displace a tosylate group from oneof the polymer ends.

B. Attachment of Polymethyloxazoline to DSPE

The terminal hydroxyl group can be converted to a carboxyl group byreaction with succinic anhydride prior to polymethyloxazoline attachmentto DSPE. Polymethyloxazoline (10 mmole) and succinic anhydride (11mmole) are mixed in 1,2-dichloroethane containing pyridine (10 mmole).The mixture is refluxed under nitrogen for four hours. After filtrationand evaporation of the solvent, the residue is dissolved in methylenechloride and precipitated twice by addition of diethyl ether. Thepolymer attachment to DSPE is performed as described for PVP.

EXAMPLE 3 Polyaspartamide Synthesis

Aspartic acid (100 g) is polymerized by heating for 2 hours at 200° C.in an open tube. This polymerization reaction results in a polymer of11,000 daltons. The polymer is dissolved in N,N-dimethylformamide andthe solution is poured into a beaker containing 1 liter of water. Aflaky precipitate is formed which is filtered, rinsed with water untilneutrality, and dried in an oven at 110° C. for 24 hours.

Poly(D,L-succinimide) (30 g) is dissolved in dimethylformamide.Ethanolamine (45 ml) is added drop by drop and the solution is cooled inan ice bath to keep the temperature at 25°-30° C. The mixture is stirredfor 2 hours and then neutralized with glacial acetic acid, diluted withwater, dialyzed and lyophilized (Neri).

The single amino group of the polymer is used for the selectiveconjugation with lipid derivatives. For example, by reductive aminationwith periodate oxidized phosphatidylglycerol or phosphatidylinositol.

Example 4 Preparation of VP/acrylamide-DSPE Conjugate

A. Polymerization of VP with Acrylamide Monomers

The VP/acrylamide copolymer is prepared in a similar fashion asdescribed for the PVP homopolymer. N-vinylpyrrolidone (60 mmole) andacrylamide (67 mmole) with 0.7 ml (10 mmole) mercaptoacetic acid (in a70% aqueous solution) and 125 mg (0.76 mmole) of AIBN is diluted to 50ml with methanol and kept at 60° C. with stirring under a nitrogenatmosphere. After 24 hours, 100 ml methylene chloride is added. Thesolution is dried over anhydrous sodium sulfate, filtered and pouredwith stirring into an excess of dry ether. The polymer is purified bydissolving in methylene chloride and reprecipitating into an excess ofdry ether.

Product is further purified by size fractionation using a Bio Gel P60column (5×50 cm) and water as the mobile phase. PVP/AA copolymers with amolecular weight of approximately 6,000 daltons (about 53 monomer units)are isolated.

B. Attachment of PVP/AA Polymer Product to DSPE

The polymer is coupled to the vesicle-forming lipid by activating thepolymer carboxyl group with N-hydroxysuccinimide prior to the additionof DSPE as described for Example 1.

EXAMPLE 5 Preparation of PEG/PVP Block Copolymer-DSPE Conjugate

A. Preparation of PEG/PVP Block Copolymer

A PVP chain containing a terminal carboxyl group is described inExample 1. Since the desired PVP product is to have an average molecularweight of about 3,000 instead of about 6,000 the concentration of MACAis increased from 0.2 M to 0.4 M. PEG chains with an average molecularweight of 2,000, each with one terminal amine and carboxyl group can besynthesized (Zalipsky). The two polymer segments are then coupled byfirst activating the PVP carboxyl group with N-hydroxysuccinimide esterand then reacting the activated carboxyl group with the amine group ofPEG.

To activate the carboxylic acid of PVP for coupling to the amine groupof PEG the following protocol is utilized. To a solution of PVP3000, 1 gin 10 ml of N,N-dimethylformamide (DMF) cooled to 10° C., and equimolaramounts of N-hydroxysuccinimide in DMF, and dicyclohexyl carbodiimide inDMF, are added dropwise. The solution is stirred overnight and thetemperature is allowed to increase to room temperature. After removal ofthe precipitate dicylohexylurea by filtration, the solution isconcentrate to dryness under high vacuum. The residue is taken up in 5ml of methylene chloride and the solution added dropwise to stirreddiethyl ether (100 ml). The white precipitate is recovered by filtrationand reprecipitated twice from methylene chloride/diethyl ether.

For attachment of PVP3000 to PEG, to a methylene chloride solution ofN-hydroxysuccinimide ester-terminated PVP (2.1 g, 0.70 mmole) is addedthe omegaamino acid derivative of PEG (1.4 g, 0.70 mmole) in 5 mlmethylene chloride followed by TEA (0.2 ml, 1.4 mmole). The reactionmixture is stirred at 25° C. for 22 hours. The product is precipitatedform the methylene chloride solution by addition of diethyl ether. Thisstep is repeated several times.

B. PVP-PEG Block Copolymer Attachment to DSPE

To activate the carboxylic acid of PVP-PEG copolymer for coupling to theamine group of DSPE the following protocol is utilized. To a solution ofPVP-PEG (MW=5000, 1 g, 0.2 mmole) in 4 ml of N,N-dimethylformamide (DMF)cooled to 10° C., and N-hydroxysuccinimide (30 mg, 0.26 mmole) in DMF (1ml), and dicyclohexyl carbodiimide (59 mg, 0.26 mmole) in DMF (1 ml),are added. The solution is stirred overnight and the temperature isallowed to increase to room temperature. After removal of theprecipitated dicylohexylurea by filtration, the solution is concentratedunder high vacuum. The residue is taken up in 5 ml of methylene chlorideand the solution added dropwise to stirred diethyl ether (100 ml). Thewhite precipitate is recovered by filtration and reprecipitated twicefrom methylene chloride/diethyl ether.

For attachment of PVP-PEG (MW=5000) to the polar head group of DSPE, tothe methylene chloride solution of N-hydroxysuccinimide ester terminatedPVP-PEG copolymer (3.5 g, 0.70 mmole) is added is added DSPE (0.70mmole) in 2 ml chloroform and TEA (0.2 ml, 1.4 mmole) are added to thereaction mixture. The mixture maintained on an oil bath heated to70°-75° C. for 2 hours. The formation of product is confirmed by TLC onsilica plates (chloroform/methanol/water/concentrated ammoniumhydroxide, (21.5/70/8/0.5).

Although the invention has been described and illustrated with respectto particular derivatized lipid compositions, it will be apparent that avariety of modifications and changes may be made without departing fromthe invention.

It is claimed:
 1. A liposomal composition containing liposomes having sizes between 0.05-0.5 microns, and comprised of vesicle-forming lipids and between 1-30 mole percent of a lipid-polymer conjugate consisting ofa lipid polymer conjugate consisting of a lipid having two hydrocarbon chains as hydrophobic moieties and a polar head group, and covalently attached to said polar head group is a homopolymer or copolymer polymer chain having one end at which the polymer chain is attached to said polar head group and an opposite free end, said polymer chain containing a polymer selected from the group consisting of polyvinylpyrrolidone, polyvinylmethylether, polyhydroxypropyl methacrylate, polyhydroxyethyl metacrylate, polyhydroxyethyl acrylate, polymethacrylamide, poly-dimethylacrylamide. polymethyloxazoline, polyethyloxazoloine, polyhydroxyproploxazoline, and polyaspartamide.
 2. The conjugate of claim 1, wherein the polymer chain is a homopolymer selected from the group consisting of polyvinylpyrrolidone, polyvinylmethylether, polyhydroxypropyl methacrylamide, polyhydroxypropyl methacrylate, polyhydroxyethyl acrylate, polymethacrylamide, polydimethylacrylamide, polymethyloxazoline, polyethyloxazoline, polyhydroxyethyloxazoline, polyhydroxypropyloxazoline, and polyaspartamide.
 3. The conjugate of claim 1, wherein the polymer chain is a block or random copolymer containing one or more blocks of a first polymer spaced by blocks or single subunits of a second polymer, said polymers selected from the group consisting of polyvinylpyrrolidone,polyvinylmethylether, polyhydroxypropyl methacrylate, polyhydroxyethyl acrylate, polymethacrylamide,and polydimethylacrylamide.
 4. The conjugate of claim 1, wherein the polymer chain is a block or random of copolymers containing one or more blocks of a first polymer spaced by blocks or single subunits of a second polymer, said polymers selected from the group consisting of polymethyloxazoline, polyethyloxazoline, polyhydroxyethyloxazoline, and polyhydroxypropyloxazoline.
 5. The conjugate of claim 1, wherein the polymer chain is a block copolymer containing one or more blocks of polyethylene glycol spaced by blocks or single subunits of a second polymer selected from the group consisting of polyvinylpyrrolidone, polyvinylmethylether, polymethacrylamide, polydimethylacrylamide, polymethyloxazoline, and polyethyloxazoline.
 6. The conjugate of claim 1, wherein the polymer is a homopolymer of polyvinylpyrrolidone.
 7. The conjugate of claim 1, wherein the polymer is a homopolymer selected from the group consisting of polymethyloxazoline and polyethyloxazoline.
 8. The conjugate of claim 1, wherein the polymer chain has degree of polymerization between about 20 to
 150. 9. The conjugate of claim 1, wherein the vesicle-forming lipid is a phospholipid.
 10. The conjugate of claim 9, wherein the vesicle-forming lipid is phosphatidylethanolamine.
 11. A method of preparing liposomes characterized by an extended blood circulation time, comprisingadding to vesicle-forming lipids, between 1-30 mole percent of a lipid-polymer conjugate consisting of a lipid polymer conjugate consisting of a lipid having two hydrocarbon chains as hydrophobic moieties and a polar head group, and covalently attached to said polar head group, is a homopolymer or copolymer chain having one end at which the polymer chain is attached to said polar head group and an opposite free end, said polymer chain containing a polymer selected from the group consisting of polyvinylpyrrolidone, polyvinylmethylether, polyhydroxypropyl methacrylamide, polyhydroxypropyl methacrylamide, polyhydroxyethyl acrylate, polymethacrylamide, polydimethylacrylamide, polymethyloxazoline, polymethyloxazoline, polyethyloxazoline, polyhydroxypropyloxazoline, and polyaspartamide, forming liposomes containing said vesicle-forming lipids and said lipid-polymer conjugate, and containing a pharmaceutical compound in entrapped form, and sizing the liposomes to a selected size in the size range between about 0.05 to 0.5 microns, where the added conjugate is effective to extend the circulation time of the liposomes when compared to liposomes prepared in the absence of said conjugate.
 12. The method of claim 11, wherein the added lipid-polymer conjugate is effective to reduce the electrophoretic mobility of the liposomes with respect to the same liposomes in which phosphatidylglycerol is substituted for said lipid polymer conjugate. 